System and method for tissue sealing

ABSTRACT

An electrosurgical system includes an energy source adapted to supply energy to tissue. The energy source includes a microprocessor configured to execute a tissue treatment algorithm configured to control the supply of electrosurgical energy to tissue and process a configuration file including at least one parameter of the tissue treatment algorithm. The at least one parameter is adjustable to effect a tissue seal result. The microprocessor generates a target impedance trajectory based on at least one parameter of the tissue treatment algorithm and is further configured to drive tissue impedance along the target impedance trajectory by adjusting the supply of energy to tissue to substantially match tissue impedance to a corresponding target impedance value. The system also includes an electrosurgical instrument including at least one active electrode adapted to apply electrosurgical energy to tissue.

BACKGROUND

1. Technical Field

The present disclosure relates to an electrosurgical system and methodfor performing electrosurgical procedures. More particularly, thepresent disclosure relates to sealing tissue, wherein energy isadministered to match measured impedance to a desired impedance.

2. Background of Related Art

Electrosurgery involves application of high radio frequency electricalcurrent to a surgical site to cut, ablate, or coagulate tissue. Inmonopolar electrosurgery, a source or active electrode delivers radiofrequency energy from the electrosurgical generator to the tissue and areturn electrode carries the current back to the generator. In monopolarelectrosurgery, the source electrode is typically part of the surgicalinstrument held by the surgeon and applied to the tissue to be treated.A patient return electrode is placed remotely from the active electrodeto carry the current back to the generator.

In bipolar electrosurgery, one of the electrodes of the hand-heldinstrument functions as the active electrode and the other as the returnelectrode. The return electrode is placed in close proximity to theactive electrode such that an electrical circuit is formed between thetwo electrodes (e.g., electrosurgical forceps). In this manner, theapplied electrical current is limited to the body tissue positionedbetween the electrodes. When the electrodes are sufficiently separatedfrom one another, the electrical circuit is open and thus inadvertentcontact of body tissue with either of the separated electrodes does notcause current to flow.

Bipolar electrosurgery generally involves the use of forceps. A forcepsis a pliers-like instruments that relies on mechanical action betweenits jaws to grasp, clamp and constrict vessels or tissue. So-called“open forceps” are commonly used in open surgical procedures whereas“endoscopic forceps” or “laparoscopic forceps” are, as the name implies,used for less invasive endoscopic or laparoscopic surgical procedures.Electrosurgical forceps (open or endoscopic) utilize mechanical clampingaction and electrical energy to effect hemostasis on the clamped tissue.The forceps include electrosurgical conductive plates that applyelectrosurgical energy to the clamped tissue. By controlling theintensity, frequency, and duration of the electrosurgical energy appliedthrough the conductive plates to tissue, the surgeon can coagulate,cauterize, and/or seal tissue.

Tissue or vessel sealing is a process of denaturing the collagen,elastin and ground substances in the tissue so that they reform into afused mass with significantly-reduced demarcation between the opposingtissue structures. Cauterization involves the use of heat to destroytissue and coagulation is a process of desiccating tissue wherein thetissue cells are ruptured and dried.

Tissue sealing procedures involve more than simply cauterizing orcoagulating tissue to create an effective seal; the procedures involveprecise control of a variety of factors. For example, in order to affecta proper seal in vessels or tissue, it has been determined that twopredominant mechanical parameters must be accurately controlled: thepressure applied to the tissue; and the gap distance between theelectrodes (i.e., the distance between opposing jaw members or opposingsealing plates). In addition, electrosurgical energy must be applied tothe tissue under controlled conditions to ensure creation of aneffective vessel seal.

SUMMARY

According to embodiments of the present disclosure, an electrosurgicalsystem includes an energy source adapted to supply energy to tissue. Theenergy source includes a microprocessor configured to execute a tissuetreatment algorithm configured to control the supply of electrosurgicalenergy to tissue and process a configuration file including at least oneparameter of the tissue treatment algorithm. The at least one parameteris adjustable to effect a tissue seal result. The microprocessorgenerates a target impedance trajectory based on at least one parameterof the tissue treatment algorithm and is further configured to drivetissue impedance along the target impedance trajectory by adjusting thesupply of energy to tissue to substantially match tissue impedance to acorresponding target impedance value. The system also includes anelectrosurgical instrument including at least one active electrodeadapted to apply electrosurgical energy to tissue.

According to another embodiment of the present disclosure, a method ofperforming an electrosurgical procedure includes the steps of adjustingat least one parameter of a tissue treatment algorithm configured tocontrol the supply of energy to tissue to effect a desired burstpressure and supplying energy from an energy source to anelectrosurgical instrument for application to tissue. The method alsoincludes the steps of generating a target impedance trajectory based onmeasured impedance and at least one parameter of the tissue treatmentalgorithm and adjusting the supply of energy from the energy source totissue to match tissue impedance to a target impedance value. The methodalso includes the step of adjusting the target impedance value to varythe desired burst pressure.

According to another embodiment of the present disclosure, a method ofperforming an electrosurgical procedure includes the steps of adjustingat least one parameter of a tissue treatment algorithm configured tocontrol the supply of energy to tissue to effect a desired burstpressure and supplying energy from an energy source to anelectrosurgical instrument for application to tissue. The method alsoincludes the steps of generating a target impedance trajectory based onmeasured impedance and a predetermined rate of change of impedance andadjusting the supply of energy from the energy source to tissue to matchtissue impedance to a target impedance value.

BRIEF DESCRIPTION OF THE DRAWINGS

Various embodiments of the present disclosure are described herein withreference to the drawings wherein:

FIG. 1A is a schematic block diagram of a monopolar electrosurgicalsystem in accordance with an embodiment of the present disclosure;

FIG. 1B is a schematic block diagram of a bipolar electrosurgical systemin accordance with an embodiment of the present disclosure;

FIG. 2 is a schematic block diagram of a generator algorithm accordingto the present disclosure;

FIG. 3 shows a flow chart illustrating a method of performing anelectrosurgical procedure; and

FIG. 4 shows a graph illustrating the changes occurring in tissueimpedance over time during an electrosurgical procedure utilizing themethod shown in FIG. 3.

DETAILED DESCRIPTION

Particular embodiments of the present disclosure will be describedhereinbelow with reference to the accompanying drawings. In thefollowing description, well-known functions or constructions are notdescribed in detail to avoid obscuring the present disclosure inunnecessary detail. Those skilled in the art will understand that thepresent disclosure may be adapted for use with either a laparoscopicinstrument or an open instrument.

It is envisioned the method may be extended to other tissue effects andenergy-based modalities including, but not limited to ultrasonic, laser,microwave, and cryo tissue treatments. It is also envisioned that thedisclosed methods are based on impedance measurement and monitoring butother tissue and energy properties may be used to determine state of thetissue, such as temperature, current, voltage, power, energy, phase ofvoltage and current. It is further envisioned that the method may becarried out using a feedback system incorporated into an electrosurgicalsystem or may be a stand-alone modular embodiment (e.g., removablemodular circuit configured to be electrically coupled to variouscomponents, such as a generator, of the electrosurgical system).

The present disclosure relates to a method for controlling energydelivery to tissue based on tissue feedback. If electrosurgical energyis being used to treat the tissue, the tissue characteristic beingmeasured and used as feedback is typically impedance and theinterrogatory signal is electrical in nature. If other energy is beingused to treat tissue then interrogatory signals and the tissueproperties being sensed vary accordingly. For instance the interrogationsignal may be achieved thermally, audibly, optically, ultrasonically,etc. and the initial tissue characteristic may then correspondingly betemperature, density, opaqueness, etc. The method according to thepresent disclosure is discussed using electrosurgical energy andcorresponding tissue properties (e.g., impedance). Those skilled in theart will appreciate that the method may be adopted using other energyapplications.

The generator according to the present disclosure can perform monopolarand bipolar electrosurgical procedures, including vessel sealingprocedures. The generator may include a plurality of outputs forinterfacing with various electrosurgical instruments (e.g., a monopolaractive electrode, return electrode, bipolar electrosurgical forceps,footswitch, etc.). Further, the generator includes electronic circuitryadapted to generate radio frequency power specifically suited forvarious electrosurgical modes (e.g., cutting, blending, division, etc.)and procedures (e.g., monopolar, bipolar, vessel sealing).

FIG. 1A is a schematic illustration of a monopolar electrosurgicalsystem according to one embodiment of the present disclosure. The systemincludes an electrosurgical instrument 2 (e.g., monopolar) having one ormore electrodes for treating tissue of a patient P (e.g.,electrosurgical cutting, ablation, etc.). More particularly,electrosurgical RF energy is supplied to the instrument 2 by a generator20 via a supply line 4, that is connected to an active terminal 30 (seeFIG. 2) of the generator 20, allowing the instrument 2 to coagulate,seal, ablate and/or otherwise treat tissue. The energy is returned tothe generator 20 through a return electrode 6 via a return line 8 at areturn terminal 32 of the generator 20 (see FIG. 2). The active terminal30 and the return terminal 32 are connectors configured to interfacewith plugs (not explicitly shown) of the instrument 2 and the returnelectrode 6, that are disposed at the ends of the supply line 4 and thereturn line 8, respectively.

FIG. 1B is a schematic illustration of a bipolar electrosurgical systemaccording to the present disclosure. The system includes a bipolarelectrosurgical forceps 10 having one or more electrodes for treatingtissue of a patient P. The electrosurgical forceps 10 includes opposingjaw members 14 and 16 having an active electrode and a return electrode(not explicitly shown), respectively, disposed thereon. The active andreturn electrodes are connected to the generator 20 through cable 18,which includes the supply and return lines 4, 8 coupled to the activeterminal 30 and return terminal 32, respectively (see FIG. 2). Theelectrosurgical forceps 10 is coupled to the generator 20 at a connector21 having connections to the active terminal 30 and return terminal 32(e.g., pins) via a plug disposed at the end of the cable 18, wherein theplug includes contacts from the supply and return lines 4, 8.

The generator 20 includes suitable input controls (e.g., buttons,activators, switches, touch screen, etc.) for controlling the generator20. In addition, the generator 20 may include one or more displayscreens for providing the user with variety of output information (e.g.,intensity settings, treatment complete indicators, etc.). The controlsallow the user to adjust power of the RF energy, waveform parameters(e.g., crest factor, duty cycle, etc.), and other parameters to achievethe desired waveform suitable for a particular task (e.g., coagulating,tissue sealing, intensity setting, etc.).

FIG. 2 shows a schematic block diagram of the generator 20 having acontroller 24, a DC power supply 27, and an RF output stage 28. Thepower supply 27 is connected to a conventional AC source (e.g.,electrical wall outlet) and is adapted to provide high voltage DC powerto an RF output stage 28 that converts high voltage DC power into RFenergy. RF output stage 28 delivers the RF energy to an active terminal30. The energy is returned thereto via the return terminal 32.

The generator 20 may include a plurality of connectors to accommodatevarious types of electrosurgical instruments (e.g., instrument 2,electrosurgical forceps 10, etc.). Further, the generator 20 may beconfigured to operate in a variety of modes such as ablation, monopolarand bipolar cutting coagulation, etc. The generator 20 may also includea switching mechanism (e.g., relays) to switch the supply of RF energybetween the connectors, such that, for example, when the instrument 2 isconnected to the generator 20, only the monopolar plug receives RFenergy.

The controller 24 includes a microprocessor 25 operably connected to amemory 26, which may be volatile type memory (e.g., RAM) and/ornon-volatile type memory (e.g., flash media, disk media, etc.). Themicroprocessor 25 includes an output port that is operably connected tothe power supply 27 and/or RF output stage 28 allowing themicroprocessor 25 to control the output of the generator 20 according toeither open and/or closed control loop schemes. Those skilled in the artwill appreciate that the microprocessor 25 may be substituted by anylogic processor (e.g., control circuit) adapted to perform thecalculations discussed herein.

A closed loop control scheme or feedback control loop is provided thatincludes a sensor circuitry 22 having one or more sensors for measuringa variety of tissue and energy properties (e.g., tissue impedance,tissue temperature, output current and/or voltage, etc.). The sensorcircuitry 22 provides feedback to the controller 24. Such sensors arewithin the purview of those skilled in the art. The controller 24 thensignals the power supply 27 and/or RF output stage 28, which thenadjusts DC and/or RF power supply, respectively. The controller 24 alsoreceives input signals from the input controls of the generator 20 orthe instrument 10. The controller 24 utilizes the input signals toadjust power outputted by the generator 20 and/or performs other controlfunctions thereon. In embodiments, sensor circuitry 22 (or an additionalsensor circuitry (not shown)) may be disposed between RF output stage 28and active terminal 30 to measure output current.

In particular, sensor circuitry 22 is adapted to measure tissueimpedance. This is accomplished by measuring voltage and current signalsand calculating corresponding impedance values as a function thereof atthe sensor circuitry 22 and/or at the microprocessor 25. Power and otherenergy properties may also be calculated based on collected voltage andcurrent signals. The sensed impedance measurements are used as feedbackby the generator 20.

The method of sealing tissue according to the present disclosure isdiscussed below with reference to FIGS. 3 and 4. The method may beembodied in a software-based tissue treatment algorithm that is storedin memory 26 and is executed by microprocessor 25. The graph of FIG. 4shows tissue impedance as a function of time to illustrate variousphases that tissue undergoes during particular application of energythereto. The decrease in tissue impedance as energy is applied occurswhen tissue is being fused (e.g., vessel sealing), ablated, ordesiccated. It is generally known that at the onset of electrical energy(i.e., during tissue fusion, ablation, or desiccation), tissue heatingresults in a decreasing impedance toward a minimum impedance value thatis below an initial sensed impedance. Tissue impedance begins to risealmost immediately when tissue is being coagulated.

Prior to or during a tissue sealing procedure, a user may select oradjust particular variables or parameters of the tissue treatmentalgorithm to effect a desired quality for a vessel seal. The quality ofa vessel seal may be determined quantitatively by burst pressure (e.g.,the pressure necessary to burst tissue at the seal site). Burst pressurefor a resulting tissue seal varies in accordance with particularparameters of the tissue treatment algorithm. The parameters of thealgorithm may correspond to one or more phases of the algorithm and mayinclude, for example without limitation, a current ramp rate parameter,an impedance ramp rate parameter, a shutoff or end tissue impedanceparameter, a seal time or procedure time parameter, a burst pressureparameter, a maximum current, a tissue impedance detection, etc. Thesealgorithm parameters may be selected/adjusted by the user through use ofthe input controls of the generator 20 and input into a configurationfile that includes a variety of variables that control the algorithm,e.g., the parameters listed above. Certain variables of theconfiguration file may be adjusted based on the instrument being usedand the settings selected by the user. One or more configuration filesmay be loaded from a data store included within controller 24.

Algorithm parameters, such as the algorithm parameters described above,may be adjusted and/or selected by a user to effect a desired burstpressure corresponding to a particular tissue seal quality. Morespecifically, by manipulating particular algorithm parameters relativeto other algorithm parameters, the resulting quality of the tissue sealmay be customized by the user. However, the adjustment of certainalgorithm parameters to achieve a desired burst pressure, may result inadded seal time to achieve the improved result. For example, the greaterthe burst pressure of a resulting tissue seal, the more seal time neededto achieve such burst pressure. The tissue treatment algorithm isconfigured to automatically make adjustments to appropriate algorithmparameters in response to and in proportion to algorithm parameters asthey are adjusted by the user. In this manner, the user may simplyselect a preset burst pressure or seal time as a tissue sealingparameter and, in response, the tissue treatment algorithm adjusts otherappropriate algorithm parameters proportionally to achieve the presetburst pressure. For example, as the user increases the desired burstpressure, the algorithm may automatically slow down a current ramp rateor an impedance ramp rate proportionally to achieve the desired burstpressure of the resulting tissue seal. Additionally or alternatively,the user may adjust a particular tissue sealing parameter (e.g., shutoffimpedance, current ramp rate, impedance ramp rate, maximum current,impedance detection, etc.) and, in response, the tissue treatmentalgorithm adjusts related algorithm parameters proportionally to effecta desired seal time, seal quality, and/or burst pressure. Further, thetissue treatment algorithm may, in certain embodiments, generate adisplay, signal, or indication of the anticipated seal time, sealquality, and/or burst pressure that will result from the user selectedparameter. For example, an indication may be provided via the displayscreen of the generator 20 as output information. Based on the outputinformation (e.g., seal time), the user is given opportunity to make aninformed revision or adjustment to algorithm parameters to increase ordecrease seal time and/or burst pressure.

During phase I or the so-called “cook phase”, which is a pre-heating orearly desiccation stage, the level of current supplied to the tissue issufficiently low and impedance of the tissue starts at an initialimpedance value. As the level of current applied to tissue is increasedor ramped upward at a predetermined rate, temperature therein rises andtissue impedance decreases. At a later point in time, tissue impedancereaches a minimum impedance value 210 that corresponds to tissuetemperature of approximately 100° C., a boiling temperature of intra-and extra-cellular fluid. The rate at which current is ramped duringphase I, for example, is an algorithm parameter that may be adjusted bythe user and loaded into the configuration file. As the current ramprate is adjusted to be slower or more gradual, the total seal time(e.g., time required to achieve a tissue seal) increases. However, asthe current ramp rate is slowed or made more gradual, the resultingburst pressure also increases to improve seal quality. Once initiated,the ramping of current continues until one of two events occurs: 1) themaximum allowable current value is reached, or 2) the tissue “reacts”.The term “tissue reaction” references a point at which intracellularand/or extra-cellular fluid begins to boil and/or vaporize, resulting inan increase in tissue impedance. In the case when the maximum allowablecurrent value is reached, the maximum current value is maintained untilthe tissue “reacts”. In the event that tissue reacts prior to reachingthe maximum current value, the level of energy required to initiate atissue “reaction” is processed and stored (e.g., in memory 26) and thetissue treatment algorithm moves to an impedance control state.

Phase II is a vaporization phase or a late desiccation phase, duringwhich tissue has achieved a phase transition from having moist andconductive properties to having dry and non-conductive properties. Inparticular, as the majority of the intra- and extra-cellular fluidsbegin to rapidly boil during the end of phase I, tissue impedance beginsto rise above the minimum impedance value 210. As sufficient energy iscontinually applied to the tissue during phase II, temperature risesbeyond the boiling point coinciding with minimum impedance value 210. Astemperature continues to rise, tissue undergoes a phase change from amoist state to a solid state and eventually to a dried-out state. Asadditional energy is applied, tissue is completely desiccated andeventually vaporized, producing steam, tissue vapors, and charring.Those skilled in the art will appreciate that the impedance changesillustrated in FIG. 4 are illustrative of an exemplary electrosurgicalprocedure and that the present disclosure may be utilized with respectto electrosurgical procedures having different impedance curves and/ortrajectories.

Once it is established that tissue has reacted, the algorithm calculatesa predefined target impedance trajectory (e.g., downward in phase I,upward in phase II, etc.) based on the actual impedance and apredetermined rate of change of the impedance (dZ/dt). The tissuetreatment algorithm controls output of the generator 20 as a function oftissue impedance by driving tissue impedance along the target impedancetrajectory by adjusting the power output level to substantially matchtissue impedance to a corresponding target impedance value. While thetissue treatment algorithm continues to direct the RF energy to drivethe tissue impedance to match the specified trajectory, the algorithmmonitors the tissue impedance to make the appropriate corrections.

As previously described, the configuration file includes a variety ofpredefined values that control the tissue treatment algorithm. Inparticular, an ending impedance value 220 and a reaction timer may beloaded into the configuration file. The ending impedance value 220, forexample, is an algorithm parameter that may be adjusted by the user andloaded into the configuration file. As the ending impedance value 220 isincreased, the total seal time (e.g., time required to achieve a tissueseal) increases and the resulting burst pressure also increases, therebyimproving the quality of the tissue seal. The desired rate of change ofthe impedance (dZ/dt) is also an algorithm parameter that may beadjusted by the user and loaded into the configuration file. As thedesired rate of change of the impedance during phase II is slowed, thetotal seal time (e.g., time required to achieve a tissue seal) increasesand the resulting burst pressure also increases, thereby improving thequality of the tissue seal.

The ending impedance value 220 in conjunction with an offset impedancevalue are used to calculate a threshold impedance value that denotescompletion of treatment. In particular, application of electrosurgicalenergy to tissue continues until tissue impedance is at or above thethreshold impedance. The threshold impedance is determined by adding theending impedance value 220 and the offset impedance value. The endingimpedance value 220 may range from about 10 ohms to about 1000 ohmsabove the lowest measured impedance reached.

The termination condition may also include applying electrosurgicalenergy for a predetermined period of time, e.g., reaction time, that isembodied by a predetermined reaction timer value loaded into theconfiguration file. This ensures that the treatment process does notover cook tissue. The ending impedance value 220 and the reaction timermay be hard-coded and may be selected automatically based on tissuetype, the instrument being used, and/or the settings selected by theuser. The ending impedance value 220 may be loaded at anytime duringtissue treatment. Further, the ending impedance value 220 and thereaction timer may also be selected/adjusted by the user.

The algorithm determines whether tissue fusion is complete by monitoringthe actual measured impedance rising above a predetermined threshold andstaying above the predetermined threshold for a predetermined period oftime. The threshold is defined as a specified level above the initialsensed impedance value and denotes completion of treatment. Thisdetermination minimizes the likelihood of terminating electrosurgicalenergy early when the tissue is not properly or completely sealed.

Referring specifically now to FIG. 3, a method of performing a tissuesealing procedure is described. In step 100, the user selects/adjustsalgorithm parameters (e.g., shutoff impedance, current ramp, impedanceramp, etc.) in accordance with a desired tissue seal result. In responsethereto, the microprocessor 25 loads the appropriate algorithmparameters into the configuration file and the generator 20 may generatea display, signal, and/or indication depicting the anticipated burstpressure and seal time that will result from the algorithm parameteradjustments selected by the user.

In embodiments, the tissue treatment algorithm simplifies for the userthe customization of tissue seal quality. For example, the user mayadjust any one or more algorithm parameters or simply select aparticular burst pressure or seal time and the algorithm willproportionally adjust appropriate algorithm parameters in responsethereto to ensure that the desired burst pressure is achieved for theresulting tissue seal. The selected parameters and/or theproportionally-adjusted parameters are processed by the microprocessor25 and loaded into the configuration file. By way of example, if theuser opts to increase the ending impedance value 220 to increase theresulting burst pressure of the tissue seal, the algorithm processes(e.g., via microprocessor 25) the ending impedance value 220 andcalculates any necessary adjustments in other algorithm parameters(e.g., current ramp, dZ/dt, seal time, etc.) to ensure that the desiredburst pressure is achieved as efficiently as possible given the selectedparameters. Once calculated, the relevant algorithm parameters may beprovided by the display screen of the generator 20. In this manner, theuser may choose to readjust certain algorithm parameters based on theinformation provided via the display screen (e.g., seal time) to eitherincrease seal quality, resulting in an increase in seal time, ordecrease seal time, resulting in a decrease in seal quality. In anotherexample, the user may opt to select a desired burst pressure. In thisscenario, the algorithm automatically adjusts the appropriate parametersproportionally to achieve the desired burst pressure as efficiently aspossible. In this manner, tailoring the seal quality is simplified inthat the user is not required to adjust specific algorithm parametersrelative to each other to achieve a desired result.

In step 110, the instrument 10 engages the tissue and the generator 20is activated (e.g., by pressing of a foot pedal or handswitch). In step120, the tissue treatment algorithm is initialized and the configurationfile is processed by microprocessor 25.

In step 130, the generator 20 supplies electrosurgical energy to thetissue through the instrument 2 or the forceps 10. During application ofenergy to the tissue, impedance is continually monitored by the sensorcircuitry 22. In particular, voltage and current signals are monitoredand corresponding impedance values are calculated at the sensorcircuitry 22 and/or at the microprocessor 25. Power and other energyproperties may also be calculated based on collected voltage and currentsignals. The microprocessor 25 stores the collected voltage, current,and impedance within the memory 26.

In step 140, an offset impedance value is obtained. The offset impedancevalue is used to calculate a threshold impedance value that denotescompletion of treatment. The threshold impedance is the sum of theending impedance value 220 and the offset impedance value. The offsetimpedance value may be obtained in multiple ways depending on theelectrosurgical procedure being performed. For example, the offsetimpedance may be tissue impedance measured at the time of maximumcurrent being passed through tissue that is required to facilitate adesired tissue effect. Using the threshold impedance value referencedand partially defined by the offset impedance value, rather than simplyan absolute value (e.g., the ending impedance value), accounts fordifferent tissue types and varying surgical devices.

Minimum measured impedance, e.g., the minimum impedance value 210, mayalso be used as the offset impedance value. This is particularly usefulwhen tissue reacts normally in a desiccation process. As shown in FIG.4, impedance drops from an initial value until the minimum impedancevalue 210 is reached. After a given time interval, the impedance risesagain at the onset of desiccation as tissue reacts. The amount of timerequired for the reaction to take place and/or the minimum impedancevalue 210 can help define various treatment parameters by identifyingtype of tissue, jaw fill or a particular device being used since theminimum impedance value 210 is aligned with the beginning stage ofdesiccation. Consequently, the offset impedance value can be captured atthe point in time when the impedance slope becomes positive, e.g., whenthe change of impedance over time (dZ/dt) is greater than zero or dZ/dtis approximately zero. Further, the offset impedance value may becalculated from a variety of different methods and utilizing a varietyof different parameters such as, for example, the starting tissueimpedance, the impedance at minimum voltage, the impedance at either apositive or negative slope change of impedance, and/or a constant valuespecified within the programming or as specified by the user and loadedin the configuration file. The starting impedance may be captured at theoutset of the application of the electrosurgical procedure via aninterrogatory pulse.

In step 150, the timing of the reaction period is commenced to ensurethat the reaction period does not exceed the reaction timer. Energyapplication continues until the threshold impedance value is reachedbefore the expiration of the reaction timer. As discussed above, energyapplication varies for different types of tissues and procedures,therefore it is desirable that the reaction timer, similar to thethreshold impedance, is also tailored to suit particular operationalrequirements. For this purpose, a time offset period is utilized. Inparticular, the time offset period is added to the reaction timer toextend the duration of energy application. Multiple time offset periodvalues may be hard-coded (e.g., in a look-up table) so that during theprocedure an appropriate value is loaded. The user may also select adesired time offset period.

In step 160, the algorithm calculates the target impedance trajectorybased on variety of values such as, for example, initial measuredimpedance, desired rate of change of impedance (dZ/dt), and the like. Inparticular, the algorithm calculates a target impedance value at eachtime-step, based on the predefined desired rate of change of impedanceover time (dZ/dt). The desired rate of change of impedance may be storedas a variable (e.g., selected by the user) and be loaded during step 100or may be selected manually or automatically based on tissue typedetermined by the selected instrument.

The target impedance takes the form of a target trajectory starting froma predetermined point (e.g., initial impedance value and time valuecorresponding to a point when tissue reaction is considered real andstable). The target trajectory may have a positive or a negative slopeand may be linear, non-linear, or quasi-linear depending on theelectrosurgical procedure being performed.

In step 170, the algorithm matches measured impedance to the targetimpedance trajectory. The algorithm adjusts the tissue impedance tomatch the target impedance. While the algorithm continues to direct theRF energy to drive the tissue impedance to match the specifiedtrajectory, the algorithm monitors the tissue impedance to make theappropriate adjustments and/or corrections.

In step 180, the algorithm determines whether tissue treatment iscomplete such that output of generator 20 should be terminated. This isdetermined by monitoring the actual measured impedance to determine ifthe actual measured impedance is at or above the predetermined thresholdimpedance. In step 190, the system monitors whether the amount of timeto reach the threshold impedance exceeds the reaction timer plus thetime offset period. If the impedance is at or above the thresholdimpedance and/or the sum of the reaction timer and the time offsetperiod has expired then the algorithm is programmed to signal completionof treatment and the generator 20 is shut off or is returned to aninitial state. The tissue treatment algorithm may also determine if themeasured impedance is greater than threshold impedance for apredetermined period of time. This determination minimizes thelikelihood of terminating electrosurgical energy early when the tissueis not properly or completely sealed.

Other tissue and/or energy properties may also be employed fordetermining termination of treatment, such as for example tissuetemperature, voltage, power and current. In particular, the algorithmanalyzes tissue properties and then acquires corresponding impedancevalues and offset times at the specified points in the tissue responseor trajectory and these values or times can be stored and/or used asabsolute or reference shut-off impedances and/or times in the mannerdiscussed above.

While several embodiments of the disclosure have been shown in thedrawings and/or discussed herein, it is not intended that the disclosurebe limited thereto, as it is intended that the disclosure be as broad inscope as the art will allow and that the specification be read likewise.Therefore, the above description should not be construed as limiting,but merely as exemplifications of particular embodiments. Those skilledin the art will envision other modifications within the scope and spiritof the claims appended hereto.

What is claimed is:
 1. An electrosurgical system, comprising: an energysource adapted to supply electrosurgical energy to tissue, the energysource including: at least one user input control for selecting a presetburst pressure parameter being a pressure at which the tissue will burstat a resulting tissue seal; a microprocessor configured to: execute atissue treatment algorithm configured to control the supply of theelectrosurgical energy to the tissue; process a configuration fileincluding at least one other parameter of the tissue treatmentalgorithm, the microprocessor configured to adjust the at least oneother parameter of the tissue treatment algorithm in response to theselected preset burst pressure parameter to control the supply of theelectrosurgical energy to the tissue to achieve a burst pressure of theresulting tissue seal equal to the selected preset burst pressureparameter; and generate a target impedance trajectory based on theprocessed configuration file, wherein the microprocessor is furtherconfigured to drive tissue impedance along the target impedancetrajectory by adjusting the supply of the electrosurgical energy to thetissue to substantially match the tissue impedance to a target impedancevalue defined at a corresponding time-step of the target impedancetrajectory; and an electrosurgical instrument including at least oneactive electrode adapted to apply the electrosurgical energy to thetissue.
 2. An electrosurgical system according to claim 1, wherein thepreset burst pressure parameter is loaded into the configuration fileprior to the supply of the electrosurgical energy to the tissue.
 3. Anelectrosurgical system according to claim 1, wherein the at least oneother parameter is selected from the group consisting of a current ramprate, a tissue impedance ramp rate, and an ending impedance value.
 4. Anelectrosurgical system according to claim 1, wherein the at least oneother parameter is a current ramp rate, wherein decreasing the currentramp rate causes at least one of an increase in a seal time and anincrease in the burst pressure of the resulting tissue seal.
 5. Anelectrosurgical system according to claim 1, wherein the at least oneother parameter is an impedance ramp rate, wherein decreasing theimpedance ramp rate causes at least one of an increase in a seal timeand an increase in the burst pressure of the resulting tissue seal. 6.An electrosurgical system according to claim 1, wherein the at least oneother parameter is the target impedance value, wherein increasing thetarget impedance value causes at least one of an increase in a seal timeand an increase in the burst pressure of the resulting tissue seal. 7.An electrosurgical system according to claim 1, wherein the at least oneother parameter is adjustable relative to at least a third parameter ofthe tissue treatment algorithm to vary the supply of the electrosurgicalenergy to the tissue.
 8. An electrosurgical system according to claim 1,wherein the microprocessor is further configured to generate a thresholdimpedance value as a function of an offset impedance value and an endingimpedance value.
 9. An electrosurgical system according to claim 1,wherein the microprocessor is further configured to compare tissueimpedance to a threshold impedance value and adjust the supply of theelectrosurgical energy to the tissue when the tissue impedance is equalto or greater than the threshold impedance value.